EP3576627B1 - Phantom - Google Patents
Phantom Download PDFInfo
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- EP3576627B1 EP3576627B1 EP18703849.2A EP18703849A EP3576627B1 EP 3576627 B1 EP3576627 B1 EP 3576627B1 EP 18703849 A EP18703849 A EP 18703849A EP 3576627 B1 EP3576627 B1 EP 3576627B1
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- European Patent Office
- Prior art keywords
- detector
- radiation
- phantom
- vessel
- test
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
- A61N5/1075—Monitoring, verifying, controlling systems and methods for testing, calibrating, or quality assurance of the radiation treatment apparatus
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/58—Testing, adjusting or calibrating apparatus or devices for radiation diagnosis
- A61B6/582—Calibration
- A61B6/583—Calibration using calibration phantoms
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
- A61N5/1075—Monitoring, verifying, controlling systems and methods for testing, calibrating, or quality assurance of the radiation treatment apparatus
- A61N2005/1076—Monitoring, verifying, controlling systems and methods for testing, calibrating, or quality assurance of the radiation treatment apparatus using a dummy object placed in the radiation field, e.g. phantom
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N5/00—Radiation therapy
- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N2005/1085—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy characterised by the type of particles applied to the patient
- A61N2005/1087—Ions; Protons
Definitions
- the present invention relates to a phantom.
- a phantom which may also be referred to as an imaging phantom or tissue equivalent phantom, is an object that is used to characterise radiation. Phantoms are usually used in medical science to mimic the response of a human body, or parts thereof, such as human organs and tissues to various stimuli, in order to prevent a living subject from being exposed to any unnecessary risk. Phantoms may be used to test responses to various kinds of radiation, including X-ray, gamma and charged particle (e.g. electrons, ions, protons) radiation. In this way, the energy deposited by the radiation is measured in order to plan treatment for individual patients.
- X-ray X-ray
- gamma charged particle radiation
- Phantoms may be used to measure the energy deposition as a function of penetration depth in a number of applications.
- the phantom It is desirable for the phantom to accurately mimic the response of a human body and to measure the radiation and its energy deposition as accurately as possible.
- US2012/0228493 may be considered to disclose a method for determining a water equivalent depth between an entrance point and a reference point; and a device according to the preamble of claim 1.
- a phantom indicated generally by a reference numeral 100.
- a phantom 100 may be used to determine the intensity, the energy deposition and the penetration depth of a beam of test radiation, such as a proton beam.
- the phantom 100 comprises a vessel 110 for containing a tissue equivalent liquid and a detector 140.
- the detector 140 may be suitable for determining the intensity, the energy or both of the beam of test radiation.
- the detector 140 is a 2-dimensional detector adapted to determine the spatial intensity and energy of the beam cross section, also referred to as the beam spot, and is movable within the vessel 110 along the path of the beam of test radiation.
- the detector 140 is supported within the vessel 110 by a support assembly.
- the vessel 110 is a cuboid tank with an open top.
- the walls of the vessel 110 are adapted to pass a beam of test radiation into the tissue equivalent liquid.
- the walls of the vessel 110 may be made out of Plexiglas or other suitable material. Preferably, the walls are made of a transparent material so that users may see inside.
- the walls of the vessel 110 may be provided with a noise suppression coating or layer so as to reduce the effects of stray radiation on the measurements.
- One wall of the vessel may include a window 150 adapted to allow the beam of test radiation to pass into the vessel.
- the window 150 may be made out of polymethyl methacrylate (PMMA) or a resin material such as that referred to as "solid water". Typically, the window material will have density close to that of water.
- PMMA polymethyl methacrylate
- solid water Typically, the window material will have density close to that of water.
- the window material should be suitable to be machined flat to a thickness of in the region of 1 mm to 3mm while still being strong enough to withstand the pressure in the vessel without distortion. It will be apparent that other suitable materials may be used.
- the window 150 may be thinner than the walls of the vessel 110. In this way, any distortion to the beam caused by the window is reduced. Further, it is possible to position the detector as close as possible to the location at which the beam enters the vessel.
- the window 150 may be between 1 mm and 2 mm thick and in a preferred arrangement is 1.3 mm thick.
- the window may be fitted in a flange that fits within a suitable hole in the front wall of the vessel.
- Figure 3 shows a drainage tube 310 and a vacuum port 320 underneath the vessel 110.
- the drainage tube 310 and the vacuum port 320 are used for drainage of the tissue equivalent liquid from the vessel 110.
- the vessel 110 is filled with a tissue equivalent liquid, for example water.
- the water may be deionized water as, advantageously, this reduces interference or errors caused by ions in the water.
- the detector 140 is supported within the vessel 110 and submerged in the tissue equivalent liquid.
- the tissue equivalent liquid is present in order to interact with the beam of test radiation, and bring it to an equilibrium within the vessel 110.
- the beam of test radiation passes into the vessel 110 through the window 150.
- the radiation source is arranged to direct the beam of test radiation along a substantially horizontal expected path in the vessel.
- the detector 140 is arranged such that its detecting surface is substantially orthogonal to the expected path of the test beam. The beam impinges on the detector 140 and its intensity is spatially determined.
- the detector 140 determines the intensity and/or energy of the beam of test radiation in at least two dimensions simultaneously.
- the detector 140 may be a silicon based detector.
- the detector 140 may be a multi-channel detector.
- the detector 140 may be a pixel detector.
- the detector 140 may be a high granularity pixel detector, and may take the form of a hybrid pixel detector or a monolithic pixel detector.
- the detector may be considered as a providing voxel-type analysis of the radiation.
- the expected path is chosen to allow the test beam of radiation to propagate into the vessel and towards the detector.
- the expected path for the test beam of radiation may typically be parallel to the sides and base of the vessel.
- the radiation may typically be a beam of charged particles, for example protons.
- the radiation may be a carbon ion beam or other suitable charged particle beam.
- the detector 140 is supported within the vessel in such a way that it may be positioned along the expected path of radiation propagating in the tissue equivalent fluid within the vessel 110. Measuring the spatial intensity of the radiation beam in at least two dimensions, perpendicular to the expected path simultaneously, and moving along the expected path, allows the intensity and energy deposition of the radiation to be precisely spatially measured in three dimensions. Thus the range of the radiation, and the position of its Bragg peak - the peak in energy deposition just before a particle is stopped by matter - may be calculated, among other things.
- a detector that may spatially determine the intensity of the radiation in two dimensions simultaneously allows a more complete view of the Bragg peak, allowing the user to determine if the beam of radiation is homogeneous in both lateral dimensions. Furthermore, as the beam of test radiation scatters in all directions, spatially determining the intensity of the test radiation in only one dimension at a time would underestimate the total intensity of the test radiation at any given time.
- the support assembly is arranged next to the vessel 110, and is arranged to provide support to the detector within the vessel.
- the support assembly comprises a linear stage 125 arranged parallel to the expected path.
- An extension arm 120 extends out from the linear stage 125 over the vessel 110, perpendicular thereto.
- the support assembly further comprises a base 170, having feet 160.
- the base 170 supports legs 180, and the vessel 110.
- the legs 180 support a platform 190.
- the linear stage 125 runs along the length of a track 195, which is set on the platform 190.
- the linear stage 125 may be motorised or manually driven to allow the position of the detector 140 along the beam to be adjusted in use with high precision.
- the extension arm 120 is connected to a tongue 130 comprising a target area 135.
- the detector 140 is mounted on the target area 135 such that it lies on the expected path of the radiation and perpendicular thereto. In this way, the detector 140 is moveable along the expected path with high precision.
- the tongue 130 is formed from a stiff material so as to prevent bending when moving in the tissue equivalent liquid. This allows the exact distance in the water between the detector 140 and the window 150 that the radiation travels to be known.
- the tongue 130 may be made out of carbon fibre but it will be apparent that other materials may be used.
- the detector 140 may be supported within the vessel 110 by other means that allow the detector be held in the path of the radiation beam and moved along the path with high precision such that its distance from the wall of the vessel, i.e. the distance along the path of the beam, can be known to high degree of accuracy. In this way, materials having a high degree of stiffness are preferred so as to substantially eliminate any flexing.
- the linear stage may provide for the extension arm 120 to be moved along the track 125 in increments.
- the size of the increments may be adjusted and may be chosen depending on the desired results. In a preferred method of operation, increments of 1 ⁇ m are used, however it will be understood that other increment sizes may be used. By using smaller increments, a highly detailed scan is obtained, however, a complete scan may take longer to complete. Therefore, it will be understood that the time for the scan may be reduced by increasing the size of the increments, but resulting in a loss of depth-wise granularity in the results.
- the detector comprises an array of individual sensors 110, each considered as a single pixel.
- the array comprises a plurality of parallel rows of sensors.
- the number of rows and columns within the array of the detector is variable, represented by the dotted lines, depending on the size of the overall matrix and individual pixels.
- the pixels of the detector 140 may be square or rectangular, or other suitable shape, with typical sizes of 50x50 ⁇ m 2 or 50x250 ⁇ m 2 , but other sizes may be used.
- the size of the full detector may be 2x2 cm 2 or other sizes.
- the detector 140 may measure up to 10x10 cm 2 or larger. Using smaller pixel sizes provides greater spatial resolution but also generates more channels to read out and increased data thus data increasing cost and complexity of a readout chain of the detector 140.
- FIG. 10 shows an example of a type of detector that may be used as part of the phantom 100.
- Figure 10 shows a vertical cross-section of a hybrid pixel array 2-D detector 1000, with individual pixels 1040 formed by a combination of two chips.
- a sensor chip 1010 comprises an array of sensor elements and has an electronics chip 1020 positioned below it such that the control electronics for each pixel are positioned directly under the sensor elements.
- the sensor elements for each detector pixel and the electronics for each detector pixel are bonded together using solder metal bumps 1030.
- the electronics elements on the electronics chip 1020 of the hybrid detector 1000 comprise the readout chain including analogue amplification and digital signal conditioning.
- the output signal from the diode may be amplified by an analogue amplifier and subsequently digitised for one or both of data storage and analysis.
- the amplified and digitized output signal may be sent to an output unit which may comprise a visual display or communication apparatus such as a network interface for transmitting data indicative of an output of each detector pixel.
- the sensor chip 1020 and the electronics chip 1010 are as thin as possible.
- the thickness of both the sensor chip 1020 and the electronics chip 1010 may typically be 50 ⁇ m. Other thicknesses of chips 1010, 1020 may be used.
- FIG. 11 there is shown another example of a type of detector that may be used as part of the phantom 100.
- Figure 11 shows a top view of a monolithic pixel detector 1100, wherein the sensor elements and associated electronics are formed on the same silicon substrate.
- the detector 140 is made up of pixel matrix 1110 and electronics circuit 1120.
- the monolithic detector 1100 of Figure 11 provides the full functionality on the same structure.
- the monolithic detector 1100 uses less silicon, as only one thickness of wafer is used instead of two for the hybrid detector 1000. This simplifies the calibration of the energy measurement, that is, the estimate of the energy deposited in water from the measurement in silicon.
- the silicon wafers used to form the various detector types typically measure 2 cm x 2cm. Therefore, detectors larger than 2x2 cm 2 are made by tiling of a single base unit detector of 2x2 cm 2 .
- Each pixel of the monolithic or hybrid detectors is constituted by a reverse biased diode providing a sensing element for the ionising radiation.
- the output signal from the diode is amplified by an analogue amplifier and subsequently digitised for data storage and analysis.
- the amplified and digitized output signal may be sent to the output unit which may comprise the visual display or the network interface.
- the amplification and digitisation can be called the readout chain.
- the readout chain is in the electronics chip and the sensor element on the sensor chip is a reverse biased diode.
- the diode, amplifier and some digital function are in each pixels and further digital functions in the periphery of the chip. This is a general scheme that can be implemented with several variants and functionalities.
- the detector types have been described as being formed from silicon, however, it will be understood that other suitable materials may be used, such as other semiconductor crystals including Silicon Carbide (SiC), Diamond, Gallium Arsenide (GaAs)
- a circular flange 1210 comprising a lip 1220, for affixing the window 150 over a hole in a wall the vessel 110.
- the flange 1210 is shown from the front in Figure 12 (a) , and a cross section A-A of the flange 1210 is shown in Figure 12 (b) .
- the flange 1210 has a number of screw holes spaced evenly around it in order to allow it to be attached to a wall of the vessel 110.
- the lip 1220 forms the inner edge of the flange 1210.
- Figure 12 (a) shows that the diameter of the lip 1220 is 65.5mm. As shown in Figure 12 (b) the lip 1220 provides a recess having a depth of 1.2mm around the inner edge of the flange to allow the window 150 to fit under it and be held in place.
- a wall 1310 of the vessel 110 having a circular central through-hole 1330.
- the central through-hole 1330 is surrounded by an annular channel 1320.
- the channel may have a depth of 1.5 mm in the wall.
- the ridge is a ring, but other suitable shapes may be envisaged.
- the channel 1320 has an inner diameter of 54mm and an outer diameter of 62mm, as labelled in Figure 13(a) .
- the flange 1210 and central through-hole combine support a window in the wall of the vessel.
- the window is preferably very thin, typically 1.3 mm and is adapted to allow the test radiation beam to pass therethrough.
- the window 150 may be held in place by the flange 1210 that may be attached to eight 5mm deep holes surrounding the window, labelled as "8 HOLE M3 x 5 DEEP ON A PCR OF 35" in Figure 13(a) .
- FIG. 4 there is shown a block diagram of the invention with the detector 140 attached to the movable support 230.
- the movable support comprises the extension arm 120, moved along the linear stage 125 by a motor 410 which is controlled by a controller 470.
- the controller 470 is adapted to send an output signal to the movable support 230 to control the position of the detector 140 along the expected path.
- a position logging module 460 is used to log the position of the movable support 230 and subsequently the position of the detector 140 inside the vessel 110.
- the position logging module 460 is adapted to receive an output signal from the movable support 230 detailing the positional information of the detector 140 and thus to log the position of the detector 140 within the vessel 110.
- the detector 140 determines the intensity and the measurement of the local energy deposition of the radiation and sends the information gathered to a vector information module 450, which is adapted to receive an output signal from detector 140 and to process information determined by the detector 140.
- the position logging module 460 may also send positional information to the vector information module 450.
- the vector information module 450 may send output signals to the controller 470 detailing the positional and vector information.
- the controller 470 may then either instruct the motor 410 to move the extension arm 120 further along the linear track 195 or, if the end of the linear track 195 has been reached, instruct the motor 410 to stop and the process to end.
- the vector information module 450 will process the information in order to determine the range and Bragg peak position of the radiation.
- the detector 140 is moved into a predetermined starting position. This may be at one end of the stage 195 or at one end of the vessel 110, or any other predetermined position. However, typically the detector starts adjacent the wall through which the test beam enters the vessel. To position the detector in the starting position, the controller 470 sends an output signal to the motor 410 of the linear stage to move the extension arm 120 into the predetermined position.
- step 520 the position of the movable support 230 (and thus the position of the detector 140 within the vessel 110) is logged.
- the movable support 230 sends an output signal detailing its position to the position logging module 460, which logs the position.
- the position logging module 460 then sends the positional information to the vector information module 450.
- the position is logged in order to match a determined intensity of radiation with the position at which it was determined, to help provide a precise three dimensional picture of the radiation.
- the detector 140 determines the intensity of the radiation in at least two dimensions, perpendicular to the longitudinal axis, simultaneously. Again, this is in order to help provide a precise three dimensional picture of the radiation.
- step 540 the information determined by the detector 140 is sent to the vector information module 450 which then processes the information.
- the vector information module 450 may determine properties of the radiation such as range in the tissue equivalent liquid, the energy deposition, the intensity and position of the Bragg peak. This is only completed in step 570 after all the information has been gathered and the full three dimensional picture of the radiation can be seen.
- the determined information is the output to be presented to the user in real time.
- step 550 position logging module 460 determines whether the movable support 230 has reached the end of the linear track 195 and sends an output signal to the controller 470 through the vector information module 450. If the end of the track has not been reached, then the controller 470 instructs the motor 410 to move the extension arm 120 along the linear track 195, and the process continues from step 520 with the extension arm 120, and thus the detector 140, further along the expected path. If the end of the track has been reached, then step 570 is completed - vector information about the radiation is determined by the vector information module 450 - and the process ends. Information from the vector information module 450 may be transmitted to a presenting means. The information may be presented to the operators in real time. The information may be stored and presented to the operators at a later time.
- FIG. 6 there is shown a simulation of the phantom in operation, measuring the intensity at a location along the define path.
- the lines travelling substantially horizontally represent the beam of test radiation, in this case a proton beam. It can be seen that the beam diverges significantly as it leaves the air and enters the vessel containing the tissue equivalent liquid.
- the detector is shown perpendicular to the beam, and it can be seen that the path of a number of the protons forming the beam pass through the detector.
- the detector 140 would have been moved from the front end of the vessel 110 (the far left of the white box in Figure 6 ) toward the back along the expected path in order to determine the intensity of the proton beam in three dimensions.
- FIG. 7 , 14 and 15 there is shown an alternative phantom, indicated generally by the reference numeral 700, comprising two spaced apart detectors, a first detector 140 and a second detector 720.
- the phantom 700 is substantially similar to the phantom 100 as shown in Figure 2 , but includes a second detector 720.
- the second detector 720 is supported in the vessel 110 along the expected path so that the two dimensions of the second detector 720 are substantially perpendicular to the expected path. Thus the second detector is substantially parallel to the first detector 140.
- the expected path is shown in the figure by a dotted line.
- the detectors 140, 720 are supported within the vessel by the support assembly.
- the two detectors 140, 720 may be arranged at a distance from 1 mm to 50 mm from each other.
- the distance between the two detectors 140, 720 may be adjustable, dependent on the conditions of the test radiation.
- Figure 14 shows a micrometre screw to control the separation between the two detectors with high accuracy. If the test radiation is a high energy beam then the detectors may advantageously be spaced further apart. If the test radiation is a low energy beam then the detectors may advantageously be spaced closer together.
- the two detectors 140, 720 may be affixed to the same tongue 130 or different tongues 130, 1410.
- the two detectors 140, 720 may be affixed by PCB holders or other suitable means. Typically, the two detectors are substantially aligned with each other.
- Figures 14 and 15(a) and (b) show an arrangement where each detector is affixed to a tongue 130, 1410, in turn mounted on an extension arm 120, 710. Both extension arms are mounted on and controlled by the linear stage.
- FIG 8 there is shown a block diagram of an alternative phantom system, comprising the alternative phantom of Figure 7 .
- this system 800 both extension arms 120, 710 are moved by the motor 410, which is also part of the movable support 230.
- the motor 410 is controlled by the controller 470.
- Both the first detector 140 and second detector 720 determine the intensity of the radiation and send the information they gathered to a vector information module 450, which acts as a processing means for data gathered by the detector 140, 720.
- the vector information module 450 is adapted to receive an output signal from the detectors 140, 720 and process information determined by the detectors 140, 720 within the vessel 110.
- the position logging module 460 may also send positional information to the vector information module 450.
- the vector information module 450 may send output signals to the controller 470 detailing the positional and vector information.
- the controller 470 may then either instruct the motor 410 to move either or both the extension arms 120, 710 further along the linear track 195 or, if the end of the linear track 195 has been reached, instruct the motor 410 to stop and the process to end.
- the vector information module 450 will process the information in order to determine the range and Bragg peak position of the radiation, as well as the direction and angle of propagation of the radiation.
- the beam of test radiation will typically be generated by a radiation therapy device used in the treatment of patients.
- the phantom may be positioned in relation to the radiation therapy device by a user to simulate the relative position of a patient to the device when the device is in use for treatment.
- the radiation therapy device may typically be configured to generate a beam having a substantially round cross section.
- the beam of radiation may have a full width at half maximum (FWHM) in the range 1 mm up to 2-3 cm. It will be understood that the beam of test radiation generated for use with the phantom will be similar to a beam of therapeutic radiation generated for use with a patient, however the therapy beam may be adjusted based on the output from the detector.
- intensity may be understood to refer to the number of particles in the beam per unit area.
- the detector of the phantom may be adapted to determine, in two dimensions, the intensity, the energy deposition or both of the test beam of radiation.
Description
- The present invention relates to a phantom.
- A phantom, which may also be referred to as an imaging phantom or tissue equivalent phantom, is an object that is used to characterise radiation. Phantoms are usually used in medical science to mimic the response of a human body, or parts thereof, such as human organs and tissues to various stimuli, in order to prevent a living subject from being exposed to any unnecessary risk. Phantoms may be used to test responses to various kinds of radiation, including X-ray, gamma and charged particle (e.g. electrons, ions, protons) radiation. In this way, the energy deposited by the radiation is measured in order to plan treatment for individual patients.
- Phantoms may be used to measure the energy deposition as a function of penetration depth in a number of applications.
- It is desirable for the phantom to accurately mimic the response of a human body and to measure the radiation and its energy deposition as accurately as possible.
-
US2012/0228493 may be considered to disclose a method for determining a water equivalent depth between an entrance point and a reference point; and a device according to the preamble of claim 1. - It is an object of embodiments of the invention to at least mitigate one or more of the problems of the prior art.
- Aspects provide a phantom and system as set forth in the appended claims.
- Embodiments of the invention are further described hereinafter with reference to the accompanying drawings, in which:
-
Figure 1 is an isometric view of an example phantom and support assembly according to the disclosure; -
Figure 2 is a simplified top view of a phantom and support assembly according to the disclosure; -
Figure 3 is a front view of the phantom and support assembly shown inFigure 1 ; -
Figure 4 is a block diagram of an example phantom with a detector inside the vessel; -
Figure 5 is a flow chart detailing the process of the phantom and support assembly in use; -
Figure 6 is an illustration of a simulation of a phantom according to the disclosure, showing radiation beams propagating through the vessel; -
Figure 7 is a simplified top view of an embodiment of a phantom having two detectors; -
Figure 8 is a block diagram of an embodiment of the phantom with two detectors; -
Figure 9 is a block diagram of an example detector for use in the phantom; -
Figure 10 is a simplified illustration of an example of a hybrid detector for use in the phantom; -
Figure 11 is a simplified illustration of an example of a monolithic detector for use in the phantom; -
Figures 12(a) and (b) are front and side cross-section views respectively of a flange for use in supporting a window in the vessel; -
Figures 13(a) and (b) are front and side cross-section views respectively is an illustration of a window and front wall of the vessel; -
Figure 14 is a perspective view of an alternative phantom comprising two detectors; and -
Figures 15(a) and (b) are perspective and exploded perspective views respectively of a portion of a support assembly for supporting two detectors in the vessel. - Referring initially to
Figures 1, 2 and3 , there is shown a phantom, indicated generally by areference numeral 100. Such aphantom 100 may be used to determine the intensity, the energy deposition and the penetration depth of a beam of test radiation, such as a proton beam. Thephantom 100 comprises avessel 110 for containing a tissue equivalent liquid and adetector 140. Thedetector 140 may be suitable for determining the intensity, the energy or both of the beam of test radiation. Thedetector 140 is a 2-dimensional detector adapted to determine the spatial intensity and energy of the beam cross section, also referred to as the beam spot, and is movable within thevessel 110 along the path of the beam of test radiation. Thedetector 140 is supported within thevessel 110 by a support assembly. - The
vessel 110 is a cuboid tank with an open top. The walls of thevessel 110 are adapted to pass a beam of test radiation into the tissue equivalent liquid. The walls of thevessel 110 may be made out of Plexiglas or other suitable material. Preferably, the walls are made of a transparent material so that users may see inside. The walls of thevessel 110 may be provided with a noise suppression coating or layer so as to reduce the effects of stray radiation on the measurements. One wall of the vessel may include awindow 150 adapted to allow the beam of test radiation to pass into the vessel. Thewindow 150 may be made out of polymethyl methacrylate (PMMA) or a resin material such as that referred to as "solid water". Typically, the window material will have density close to that of water. The window material should be suitable to be machined flat to a thickness of in the region of 1 mm to 3mm while still being strong enough to withstand the pressure in the vessel without distortion. It will be apparent that other suitable materials may be used. Advantageously, thewindow 150 may be thinner than the walls of thevessel 110. In this way, any distortion to the beam caused by the window is reduced. Further, it is possible to position the detector as close as possible to the location at which the beam enters the vessel. Thewindow 150 may be between 1 mm and 2 mm thick and in a preferred arrangement is 1.3 mm thick. The window may be fitted in a flange that fits within a suitable hole in the front wall of the vessel. -
Figure 3 shows adrainage tube 310 and avacuum port 320 underneath thevessel 110. Thedrainage tube 310 and thevacuum port 320 are used for drainage of the tissue equivalent liquid from thevessel 110. - In use, the
vessel 110 is filled with a tissue equivalent liquid, for example water. The water may be deionized water as, advantageously, this reduces interference or errors caused by ions in the water. Thedetector 140 is supported within thevessel 110 and submerged in the tissue equivalent liquid. The tissue equivalent liquid is present in order to interact with the beam of test radiation, and bring it to an equilibrium within thevessel 110. The beam of test radiation passes into thevessel 110 through thewindow 150. Typically, the radiation source is arranged to direct the beam of test radiation along a substantially horizontal expected path in the vessel. Thedetector 140 is arranged such that its detecting surface is substantially orthogonal to the expected path of the test beam. The beam impinges on thedetector 140 and its intensity is spatially determined. Thedetector 140 determines the intensity and/or energy of the beam of test radiation in at least two dimensions simultaneously. Thedetector 140 may be a silicon based detector. Thedetector 140 may be a multi-channel detector. Thedetector 140 may be a pixel detector. Thedetector 140 may be a high granularity pixel detector, and may take the form of a hybrid pixel detector or a monolithic pixel detector. - Given that the pixel detector provides detection in two dimensions and is movable in a third dimension, it will be understood that the detector may be considered as a providing voxel-type analysis of the radiation. The expected path is chosen to allow the test beam of radiation to propagate into the vessel and towards the detector. In a cuboid vessel, the expected path for the test beam of radiation may typically be parallel to the sides and base of the vessel. The radiation may typically be a beam of charged particles, for example protons. The radiation may be a carbon ion beam or other suitable charged particle beam.
- The
detector 140 is supported within the vessel in such a way that it may be positioned along the expected path of radiation propagating in the tissue equivalent fluid within thevessel 110. Measuring the spatial intensity of the radiation beam in at least two dimensions, perpendicular to the expected path simultaneously, and moving along the expected path, allows the intensity and energy deposition of the radiation to be precisely spatially measured in three dimensions. Thus the range of the radiation, and the position of its Bragg peak - the peak in energy deposition just before a particle is stopped by matter - may be calculated, among other things. - Precise knowledge of the Bragg peak and range of the charged particle beam in three dimensions allows predetermined areas to be targeted to receive the maximal dosage from the beam. The radiation will deliver a relatively small dose to matter it interacts with before the peak, and the dose falls off rapidly after the peak. This means that in cancer radiotherapy, a patient may have their tumour targeted by radiation by arranging that the Bragg peak of the beam is located within the tumour, with a smaller dose being delivered to the surrounding healthy tissues.
- The presence of a detector that may spatially determine the intensity of the radiation in two dimensions simultaneously allows a more complete view of the Bragg peak, allowing the user to determine if the beam of radiation is homogeneous in both lateral dimensions. Furthermore, as the beam of test radiation scatters in all directions, spatially determining the intensity of the test radiation in only one dimension at a time would underestimate the total intensity of the test radiation at any given time.
- The support assembly is arranged next to the
vessel 110, and is arranged to provide support to the detector within the vessel. The support assembly comprises alinear stage 125 arranged parallel to the expected path. Anextension arm 120 extends out from thelinear stage 125 over thevessel 110, perpendicular thereto. The support assembly further comprises abase 170, havingfeet 160. Thebase 170 supportslegs 180, and thevessel 110. Thelegs 180 support aplatform 190. Thelinear stage 125 runs along the length of atrack 195, which is set on theplatform 190. Thelinear stage 125 may be motorised or manually driven to allow the position of thedetector 140 along the beam to be adjusted in use with high precision. - The
extension arm 120 is connected to atongue 130 comprising atarget area 135. Thedetector 140 is mounted on thetarget area 135 such that it lies on the expected path of the radiation and perpendicular thereto. In this way, thedetector 140 is moveable along the expected path with high precision. Preferably thetongue 130 is formed from a stiff material so as to prevent bending when moving in the tissue equivalent liquid. This allows the exact distance in the water between thedetector 140 and thewindow 150 that the radiation travels to be known. In a preferred example, thetongue 130 may be made out of carbon fibre but it will be apparent that other materials may be used. It will be understood that thedetector 140 may be supported within thevessel 110 by other means that allow the detector be held in the path of the radiation beam and moved along the path with high precision such that its distance from the wall of the vessel, i.e. the distance along the path of the beam, can be known to high degree of accuracy. In this way, materials having a high degree of stiffness are preferred so as to substantially eliminate any flexing. - The linear stage may provide for the
extension arm 120 to be moved along thetrack 125 in increments. The size of the increments may be adjusted and may be chosen depending on the desired results. In a preferred method of operation, increments of 1µm are used, however it will be understood that other increment sizes may be used. By using smaller increments, a highly detailed scan is obtained, however, a complete scan may take longer to complete. Therefore, it will be understood that the time for the scan may be reduced by increasing the size of the increments, but resulting in a loss of depth-wise granularity in the results. - Referring now to
Figure 9 , there is shown a simplified representation of an example detector for use in the phantom, indicated generally by thereference numeral 140. The detector comprises an array ofindividual sensors 110, each considered as a single pixel. The array comprises a plurality of parallel rows of sensors. The number of rows and columns within the array of the detector is variable, represented by the dotted lines, depending on the size of the overall matrix and individual pixels. - The pixels of the
detector 140 may be square or rectangular, or other suitable shape, with typical sizes of 50x50 µm2 or 50x250 µm2, but other sizes may be used. The size of the full detector may be 2x2 cm2 or other sizes. Thedetector 140 may measure up to 10x10 cm2 or larger. Using smaller pixel sizes provides greater spatial resolution but also generates more channels to read out and increased data thus data increasing cost and complexity of a readout chain of thedetector 140. - Referring to
Figure 10 , there is shown an example of a type of detector that may be used as part of thephantom 100.Figure 10 shows a vertical cross-section of a hybrid pixel array 2-D detector 1000, withindividual pixels 1040 formed by a combination of two chips. Asensor chip 1010 comprises an array of sensor elements and has anelectronics chip 1020 positioned below it such that the control electronics for each pixel are positioned directly under the sensor elements. The sensor elements for each detector pixel and the electronics for each detector pixel are bonded together using solder metal bumps 1030. - The electronics elements on the
electronics chip 1020 of thehybrid detector 1000 comprise the readout chain including analogue amplification and digital signal conditioning. The output signal from the diode may be amplified by an analogue amplifier and subsequently digitised for one or both of data storage and analysis. The amplified and digitized output signal may be sent to an output unit which may comprise a visual display or communication apparatus such as a network interface for transmitting data indicative of an output of each detector pixel. - Preferably, the
sensor chip 1020 and theelectronics chip 1010 are as thin as possible. The thickness of both thesensor chip 1020 and theelectronics chip 1010 may typically be 50 µm. Other thicknesses ofchips - Referring to
Figure 11 , there is shown another example of a type of detector that may be used as part of thephantom 100.Figure 11 shows a top view of amonolithic pixel detector 1100, wherein the sensor elements and associated electronics are formed on the same silicon substrate. Thedetector 140 is made up ofpixel matrix 1110 andelectronics circuit 1120. In comparison to thehybrid detector 1000 ofFigure 10 , themonolithic detector 1100 ofFigure 11 provides the full functionality on the same structure. - Advantageously, the
monolithic detector 1100 uses less silicon, as only one thickness of wafer is used instead of two for thehybrid detector 1000. This simplifies the calibration of the energy measurement, that is, the estimate of the energy deposited in water from the measurement in silicon. - The silicon wafers used to form the various detector types typically measure 2 cm x 2cm. Therefore, detectors larger than 2x2 cm2 are made by tiling of a single base unit detector of 2x2 cm2.
- Each pixel of the monolithic or hybrid detectors is constituted by a reverse biased diode providing a sensing element for the ionising radiation. The output signal from the diode is amplified by an analogue amplifier and subsequently digitised for data storage and analysis. The amplified and digitized output signal may be sent to the output unit which may comprise the visual display or the network interface. The amplification and digitisation can be called the readout chain. In the hybrid version the readout chain is in the electronics chip and the sensor element on the sensor chip is a reverse biased diode. In the monolithic version the diode, amplifier and some digital function are in each pixels and further digital functions in the periphery of the chip. This is a general scheme that can be implemented with several variants and functionalities.
- The detector types have been described as being formed from silicon, however, it will be understood that other suitable materials may be used, such as other semiconductor crystals including Silicon Carbide (SiC), Diamond, Gallium Arsenide (GaAs)
- Referring now to
Figure 12 , there is shown acircular flange 1210, comprising alip 1220, for affixing thewindow 150 over a hole in a wall thevessel 110. Theflange 1210 is shown from the front inFigure 12 (a) , and a cross section A-A of theflange 1210 is shown inFigure 12 (b) . Theflange 1210 has a number of screw holes spaced evenly around it in order to allow it to be attached to a wall of thevessel 110. Thelip 1220 forms the inner edge of theflange 1210. -
Figure 12 (a) shows that the diameter of thelip 1220 is 65.5mm. As shown inFigure 12 (b) thelip 1220 provides a recess having a depth of 1.2mm around the inner edge of the flange to allow thewindow 150 to fit under it and be held in place. - Referring to
Figure 13 , there is shown awall 1310 of thevessel 110 having a circular central through-hole 1330. The central through-hole 1330 is surrounded by anannular channel 1320. The channel may have a depth of 1.5 mm in the wall. The ridge is a ring, but other suitable shapes may be envisaged. Thechannel 1320 has an inner diameter of 54mm and an outer diameter of 62mm, as labelled inFigure 13(a) . Theflange 1210 and central through-hole combine support a window in the wall of the vessel. The window is preferably very thin, typically 1.3 mm and is adapted to allow the test radiation beam to pass therethrough. - The
window 150 may be held in place by theflange 1210 that may be attached to eight 5mm deep holes surrounding the window, labelled as "8 HOLE M3 x 5 DEEP ON A PCR OF 35" inFigure 13(a) . - Referring now to
Figure 4 , there is shown a block diagram of the invention with thedetector 140 attached to themovable support 230. The movable support comprises theextension arm 120, moved along thelinear stage 125 by amotor 410 which is controlled by acontroller 470. - The
controller 470 is adapted to send an output signal to themovable support 230 to control the position of thedetector 140 along the expected path. - A
position logging module 460 is used to log the position of themovable support 230 and subsequently the position of thedetector 140 inside thevessel 110. Theposition logging module 460 is adapted to receive an output signal from themovable support 230 detailing the positional information of thedetector 140 and thus to log the position of thedetector 140 within thevessel 110. - The
detector 140 determines the intensity and the measurement of the local energy deposition of the radiation and sends the information gathered to avector information module 450, which is adapted to receive an output signal fromdetector 140 and to process information determined by thedetector 140. Theposition logging module 460 may also send positional information to thevector information module 450. - The
vector information module 450 may send output signals to thecontroller 470 detailing the positional and vector information. Thecontroller 470 may then either instruct themotor 410 to move theextension arm 120 further along thelinear track 195 or, if the end of thelinear track 195 has been reached, instruct themotor 410 to stop and the process to end. Thevector information module 450 will process the information in order to determine the range and Bragg peak position of the radiation. - Referring now to
Figure 5 , there is shown a flow chart detailing amethod 500 of operation of the system ofFigure 4 . Atstep 510, thedetector 140 is moved into a predetermined starting position. This may be at one end of thestage 195 or at one end of thevessel 110, or any other predetermined position. However, typically the detector starts adjacent the wall through which the test beam enters the vessel. To position the detector in the starting position, thecontroller 470 sends an output signal to themotor 410 of the linear stage to move theextension arm 120 into the predetermined position. - Next, in
step 520 the position of the movable support 230 (and thus the position of thedetector 140 within the vessel 110) is logged. Themovable support 230 sends an output signal detailing its position to theposition logging module 460, which logs the position. Theposition logging module 460 then sends the positional information to thevector information module 450. The position is logged in order to match a determined intensity of radiation with the position at which it was determined, to help provide a precise three dimensional picture of the radiation. - In
step 530, thedetector 140 determines the intensity of the radiation in at least two dimensions, perpendicular to the longitudinal axis, simultaneously. Again, this is in order to help provide a precise three dimensional picture of the radiation. - In
step 540, the information determined by thedetector 140 is sent to thevector information module 450 which then processes the information. Thevector information module 450 may determine properties of the radiation such as range in the tissue equivalent liquid, the energy deposition, the intensity and position of the Bragg peak. This is only completed instep 570 after all the information has been gathered and the full three dimensional picture of the radiation can be seen. The determined information is the output to be presented to the user in real time. - In
step 550,position logging module 460 determines whether themovable support 230 has reached the end of thelinear track 195 and sends an output signal to thecontroller 470 through thevector information module 450. If the end of the track has not been reached, then thecontroller 470 instructs themotor 410 to move theextension arm 120 along thelinear track 195, and the process continues fromstep 520 with theextension arm 120, and thus thedetector 140, further along the expected path. If the end of the track has been reached, then step 570 is completed - vector information about the radiation is determined by the vector information module 450 - and the process ends. Information from thevector information module 450 may be transmitted to a presenting means. The information may be presented to the operators in real time. The information may be stored and presented to the operators at a later time. - Referring now to
Figure 6 , there is shown a simulation of the phantom in operation, measuring the intensity at a location along the define path. The lines travelling substantially horizontally represent the beam of test radiation, in this case a proton beam. It can be seen that the beam diverges significantly as it leaves the air and enters the vessel containing the tissue equivalent liquid. The detector is shown perpendicular to the beam, and it can be seen that the path of a number of the protons forming the beam pass through the detector. - It can be seen from this figure how the radiation spreads through the tissue equivalent liquid, propagating towards the
detector 140, along the expected path. In this example, thedetector 140 would have been moved from the front end of the vessel 110 (the far left of the white box inFigure 6 ) toward the back along the expected path in order to determine the intensity of the proton beam in three dimensions. - Referring now to
Figures 7 ,14 and15 (a) and (b) , there is shown an alternative phantom, indicated generally by thereference numeral 700, comprising two spaced apart detectors, afirst detector 140 and asecond detector 720. Thephantom 700 is substantially similar to thephantom 100 as shown inFigure 2 , but includes asecond detector 720. Thesecond detector 720 is supported in thevessel 110 along the expected path so that the two dimensions of thesecond detector 720 are substantially perpendicular to the expected path. Thus the second detector is substantially parallel to thefirst detector 140. The expected path is shown in the figure by a dotted line. As inFigure 2 , thedetectors - Two measurements made at different points along the expected path simultaneously, one by each of the
first detector 140 andsecond detector 720, allow the direction and angle of propagation of the radiation entering the vessel to be determined, and provide the local divergence of the beam. - The two
detectors detectors Figure 14 shows a micrometre screw to control the separation between the two detectors with high accuracy. If the test radiation is a high energy beam then the detectors may advantageously be spaced further apart. If the test radiation is a low energy beam then the detectors may advantageously be spaced closer together. - The two
detectors same tongue 130 ordifferent tongues detectors -
Figures 14 and15(a) and (b) show an arrangement where each detector is affixed to atongue extension arm - Referring now to
Figure 8 , there is shown a block diagram of an alternative phantom system, comprising the alternative phantom ofFigure 7 . In thissystem 800, bothextension arms motor 410, which is also part of themovable support 230. Themotor 410 is controlled by thecontroller 470. - Both the
first detector 140 andsecond detector 720 determine the intensity of the radiation and send the information they gathered to avector information module 450, which acts as a processing means for data gathered by thedetector vector information module 450 is adapted to receive an output signal from thedetectors detectors vessel 110. Theposition logging module 460 may also send positional information to thevector information module 450. - The
vector information module 450 may send output signals to thecontroller 470 detailing the positional and vector information. Thecontroller 470 may then either instruct themotor 410 to move either or both theextension arms linear track 195 or, if the end of thelinear track 195 has been reached, instruct themotor 410 to stop and the process to end. Thevector information module 450 will process the information in order to determine the range and Bragg peak position of the radiation, as well as the direction and angle of propagation of the radiation. - The beam of test radiation will typically be generated by a radiation therapy device used in the treatment of patients. The phantom may be positioned in relation to the radiation therapy device by a user to simulate the relative position of a patient to the device when the device is in use for treatment. The radiation therapy device may typically be configured to generate a beam having a substantially round cross section. The beam of radiation may have a full width at half maximum (FWHM) in the range 1 mm up to 2-3 cm. It will be understood that the beam of test radiation generated for use with the phantom will be similar to a beam of therapeutic radiation generated for use with a patient, however the therapy beam may be adjusted based on the output from the detector.
- Throughout the description and claims of this specification, the term intensity may be understood to refer to the number of particles in the beam per unit area. Throughout the description and claims, it will be understood that the detector of the phantom may be adapted to determine, in two dimensions, the intensity, the energy deposition or both of the test beam of radiation.
- Throughout the description and claims of this specification, the words "comprise" and "contain" and variations of them mean "including but not limited to", and they are not intended to (and do not) exclude other moieties, additives, components, integers or steps. Throughout the description and claims of this specification, the singular encompasses the plural unless the context otherwise requires. In particular, where the indefinite article is used, the specification is to be understood as contemplating plurality as well as singularity, unless the context requires otherwise.
Claims (14)
- A phantom (700) comprising
a vessel (110) for containing a tissue equivalent liquid and adapted to pass a beam of test radiation into the vessel,
a first detector (140) adapted to determine the intensity of the beam of test radiation, the first detector being supported within the vessel (110) and movable therein along a path of the beam of test radiation;
wherein the first detector (140) is a 2-dimensional detector adapted to determine the spatial intensity of the beam,
wherein the phantom (700) is characterised in that it further comprises a second detector (720) collinear with and spaced apart from the first detector (140), the second detector (720) also being supported within the vessel (110) and movable therein along the path of the beam of test radiation in line with the first detector (140), wherein the second detector (720) is a 2-dimensional detector adapted to determine the spatial intensity of the beam. - The phantom (700) of claim 1 wherein the vessel (110) comprises at least one wall having a window (150) therein, which window (150) is adapted to pass the beam of test radiation to the tissue equivalent liquid.
- The phantom (700) of claim 1 or 2, wherein at least one of the first detector (140) and the second detector (720) is silicon based.
- The phantom (700) of any preceding claim, wherein at least one of the first detector (140) and the second detector (720) is a multi-channel detector such as a pixel detector array.
- The phantom (700) of any preceding claim, wherein the vessel (110) contains a tissue equivalent liquid.
- The phantom (700) of claim 5, wherein the tissue equivalent liquid is water.
- The phantom (700) of claim 6, wherein the water is deionised water.
- The phantom (700) of any preceding claim wherein the path of the beam of test radiation is substantially horizontal.
- The phantom (700) of any preceding claim wherein the distance between the first detector (140) and the second detector (720) is adjustable.
- A radiation detection system, comprising the phantom (700) of any preceding claim; and
a driven movable support (230) for the detectors adapted to move the first detector (140) and second detector (720) along the path of the beam of test radiation;
a controller (470) adapted to control the position of the first detector (140) and second detector (720);
a position logging module (460) adapted to log the position of the first detector (140) and the second detector (720) within the vessel (110);
a vector information module (450) adapted to receive an output signal from each of the first detector (140) the second detector and process information determined by the first detector (140) and second detector (720). - A radiation detection system as claimed in claim 10 wherein driven movable support (230) comprises a linear stage (125).
- A radiation detection system as claimed in claim 9 or 10 wherein the vector information module (450) is configured to determine the direction and angle of propagation of the beam of test radiation.
- A radiation detection system as claimed in any of claims 9 to 11 wherein the vector information module (450) is configured to determine the energy deposition of the beam of test radiation.
- A method of operating the phantom of claim 1, the detectors being attached to a support (230), said support being adapted to move along a linear track (125), and which is adapted to send an output signal detailing its position to a position logging module (460), and thus log the position of the detector/s within the vessel, the method comprising,
for each of a plurality of detector positions along the radiation beam, the position logging modulelogging the position of the detectors in the phantom (700);determining the intensity of the radiation;providing the determined intensity and the detector position to a vector information module (450);moving the at least one detector to a subsequent position along the radiation beam until the end of the track has been reached; andthe vector information module determining the Bragg peak position of the radiation beam from the determined intensities at the plurality of detector positions.
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